![]() ![]() ![]() ![]() With rapid advances in medical imaging and computational techniques, three-dimensional (3D) realistic airway geometries with major branches derived from high resolution computed tomography (CT) images have recently been used in CFD analyses ( Choi et al., 2009 Freitas and Schröder, 2008 Lin et al., 2007, 2009). Although those studies provide some insights into the characteristics of flow in systems of bifurcating tubes, their idealized airway models lack subject-specific geometrical features for assessing an individual’s response to inhaled particulates and for better tailoring a treatment plan for the individual. Due to the complexity of the human tracheobronchial tree, most earlier CFD studies of pulmonary air flow used either the symmetric Weibel (1963) model or the asymmetric Horsfield et al. Since particle deposition is highly dependent on flow characteristics, which, in turn, are dependent on the geometrical configuration of airways and regional ventilation of the lungs, it is desirable to conduct subject-specific CFD with an anatomically realistic airway geometry and a physiologically consistent boundary condition (BC). One of its applications is to predict the local deposition of pollutant or therapeutic particles for the purpose of understanding the etiology of lung pathology and for the improvement of drug delivery methods. (2003), Ma and Lutchen (2009), Stapleton et al. A representative though not exhaustive list of such studies can be found in Choi et al. Computational fluid dynamics (CFD) has become a vital tool in understanding the nature of pulmonary air flow in the human lungs from the large central bronchial airways to the acinar regions. ![]()
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